JP4722481B2 - Liposome production method and apparatus - Google Patents

Abstract

The present invention provides apparatus and processes for producing a lipid vesicle encapsulating one or more therapeutic agents within the lipid vesicle. By providing a aqueous solution in a first reservoir and an organic lipid solution in a second reservoir. The said aqueous solution and/or said organic lipid solution comprises one or more therapeutic agents. The organic lipid solution is mixed with the aqueous solution by introducing the organic lipid solution and the aqueous solution into a mixing environment at about equal flow rates. The said mixing instantaneously produces a lipid vesicle encapsulating said one or more therapeutic agents within the lipid vesicle.

Description

(Cross-reference of related applications)
This application is a non-provisional application of US Provisional Patent Application No. 60 / 392,887, filed June 28, 2002, and claims priority to this provisional application. This provisional application is incorporated herein by reference in its entirety.

(Background of the Invention)
Many systems are already known for administering agents into cells, such as liposomes, nanoparticles, polymer particles, immune and ligand complexes, and cyclodextrins ("in antibacterial and anticancer chemotherapy"). Drug Transport (see Antibiotic and Anticancer Chemotherapy), edited by G. Papadakuou, CRC Press, 1995). Liposomes are generally prepared in the laboratory by sonication, detergent dialysis, ethanol injection or dilution, French press extrusion, ether injection, and reverse phase evaporation. Liposomes with multiple bilayers are known as multilamellar lipid vesicles (MLV). Since only the liquid trapped between the layers is released as each membrane degrades, MLV is a candidate for a long acting drug. Liposomes with a single bilayer are known as unilamellar lipid vesicles (UV). The UV can be small (SUV) or large (LUV).

  Some of the methods described above for liposome production impose harsh and extreme conditions that can cause denaturation of the phospholipid raw material and the encapsulated drug. Moreover, in these methods, it is not easy to expand the scale in order to mass-produce large quantities of liposomes. Furthermore, in conventional lipid vesicle formation by ethanol dilution, it is necessary to add lipids while injecting or dropping them in an aqueous buffer solution. The vesicles thus obtained are generally non-uniform in size and contain a mixture of monolayer and multilayer vesicles.

  Conventional liposomes are formulated to deliver a therapeutic agent contained either in an aqueous interior space (water-soluble drug) or a lipid bilayer (water-insoluble drug). Active agents that have a short half-life in the bloodstream are particularly suitable for delivery via liposomes. For example, many anti-neoplastic agents are known to be inappropriate for parenteral use due to their short half-life in the bloodstream. However, the use of liposomes for site-specific delivery of active agents via the bloodstream is severely limited by the rapid clearance of liposomes from the blood by reticuloendothelial (RES) cells.

  US Patent No. 5,478,860 issued to Wheeler et al., Issued December 26, 1995, incorporated herein by reference, discloses microemulsion compositions for the delivery of hydrophobic compounds. Such compositions have a variety of uses. In one embodiment, the hydrophobic compound is a therapeutic agent including a drug. This patent also discloses methods for in vitro and in vivo delivery of hydrophobic compounds to cells.

  In Nopoy et al. PCT Publication No. 01/05373, which is incorporated herein by reference, lipid vesicles using an ethanol injection type process with a static mixer that provides a turbulent environment (eg, Reynolds number> 2000). Discloses a method for preparing the. Subsequently, a therapeutic agent may be introduced after vesicle formation.

  Process for formulating and manufacturing lipid vesicles, particularly lipid vesicles encapsulating therapeutic agents such as nucleic acids, despite the obvious progress of US Pat. No. 5,478,860 and WO 05373 And there is a need for equipment. The present invention satisfies the foregoing and other needs.

(Summary of Invention)
The present invention provides a process and apparatus for producing lipid vesicles optionally comprising a therapeutic agent. The therapeutic agent can include, for example, a protein, nucleic acid, antisense nucleic acid, drug, or the like. The present invention can be used to form lipid vesicles containing encapsulated plasmid DNA or small molecule drugs. In one embodiment, lipid vesicles are rapidly prepared at low pressure, and this approach is completely scalable. In certain preferred embodiments, the process does not include a static mixer or dedicated extrusion equipment.

  Similarly, in one embodiment, the present invention provides a process for producing liposomes. This process generally comprises providing an aqueous solution to the organic lipid solution of the second reservoir and the first reservoir in liquid flow, and further mixing the aqueous solution with the organic lipid solution to produce organic to produce liposomes. The lipid solution is diluted in successive steps.

  In certain embodiments, an aqueous solution, such as a buffer, includes a therapeutic agent, such as an encapsulated therapeutic agent in a liposome. Preferred therapeutic agents include, but are not limited to, proteins, nucleic acids, antisense nucleic acids, ribozymes, tRNA, snRNA, siRNA (small interfering RNA), pre-concentrated DNA, and antigens. In certain preferred embodiments, the therapeutic agent is a nucleic acid.

  In another embodiment, the present invention provides a process for producing liposomes encapsulating a therapeutic agent. This process generally comprises providing an aqueous solution to a first reservoir and providing an organic lipid solution to a second reservoir, wherein one of the aqueous solution or the organic lipid solution contains a therapeutic agent. . In addition, the process generally includes mixing the aqueous solution with the organic lipid solution, where the organic lipid solution is mixed with the aqueous solution to produce liposomes that encapsulate the therapeutic agent substantially instantaneously. In some embodiments, the therapeutic agent is a nucleic acid contained in an aqueous solution. In some embodiments, the therapeutic agent is lipophilic and is included in the organic lipid solution. In certain embodiments, the encapsulation efficiency of the initial therapeutic agent is about 90%.

  In yet another embodiment, the present invention provides an apparatus for producing liposomes encapsulating a therapeutic agent. The apparatus generally includes a first reservoir for holding an aqueous solution and a second reservoir for holding an organic lipid solution, one of the aqueous solution and the organic lipid solution containing a therapeutic agent. The apparatus also generally includes a pump mechanism comprised of a mechanism for pumping the aqueous solution and the organic lipid solution at substantially equal flow rates into the mixing region. In use, the organic lipid solution is mixed with the aqueous solution in this mixing region, and liposomes encapsulating the therapeutic agent are formed substantially instantaneously.

  The foregoing and other aspects will become more apparent when read in conjunction with the accompanying drawings and the following detailed description.

(Detailed description of the invention)
(I. Definition)
The term “nucleic acid” refers to a polymer comprising at least two nucleotides. “Nucleotides” include sugar deoxyribose (DNA) or ribose (RNA), bases, and phosphate groups. Nucleotides are linked to each other by phosphate groups. “Base” refers to purines and pyrimidines that further include the natural compounds adenine, thymine, guanine, cytosine, uracil, inosine, and natural analogs, and include, but are not limited to, amines, alcohols, thiols, Acid esters, and synthetic derivatives of purines and pyrimidines, including but not limited to modifications that introduce new reactive groups such as alkyl halides.

  DNA is antisense, plasmid DNA, plasmid DNA portion, pre-concentrated DNA, polymerase chain reaction (PCR) product, vectors (P1, PAC, BAC, YAC, artificial chromosome), expression cassette, chimeric sequence, chromosomal DNA Alternatively, it may have the form of these groups of derivatives. RNA is oligonucleotide RNA, tRNA (transfer RNA), snRNA (nuclear small RNA), rRNA (liposomal RNA), mRNA (messenger RNA), antisense RNA, siRNA (small RNA in RNA interference process), ribozyme, It can have the form of a chimeric sequence, or a derivative of these groups.

  “Antisense” is a polynucleotide that interferes with the function of DNA and / or RNA. For this reason, expression is suppressed. Natural nucleic acids have a phosphate backbone, and artificial nucleic acids contain other types of backbones and bases. These include PNA (peptide nucleic acids), phosphothionates, and variants of the phosphate backbone of other natural nucleic acids. Furthermore, DNA and RNA are single, double, triple or quadruplex.

  “Gene” refers to a sequence of nucleic acids (eg, DNA) comprising coding sequences necessary for the production of a polypeptide or precursor (eg, herpes simplex virus). As long as the desired activity or functional properties of the full length or fragment are retained (eg, enzymatic activity, ligand binding, signal transduction, and the like), the polypeptide can be expressed as a full length coding sequence, or any coding sequence Can be coded by

  As used herein, the term “aqueous solution” refers to a composition that contains water in whole or in part.

  As used herein, the term “organic lipid solution” refers to a composition comprising an organic solvent having lipids in whole or in part.

  The term “lipid” refers to a group of organic compounds that are esters of fatty acids and are characterized by being insoluble in water but soluble in many organic solvents. They are usually divided into at least three classes. That is, (1) “simple lipid” containing fats and oils in addition to wax, (2) “complex lipid” containing phospholipid and glycolipid, and (3) “derived lipid” such as steroid.

  The term “amphiphilic lipid” means any suitable material in which the hydrophobic portion of the lipid material is partially oriented in the hydrophobic phase while the hydrophilic portion is oriented in the aqueous phase. Amphiphilic lipids are usually the main component of lipid vesicles. The hydrophilic properties are derived from the presence of polar or charged groups such as carbohydrates, phosphate groups, carboxylic acid groups, sulfate groups, amino groups, sulfhydryl groups, nitro groups, hydroxy groups and other groups. Hydrophobicity includes, but is not limited to, long chain saturated and unsaturated aliphatic hydrocarbon groups and functional group (s) substituted with one or more aromatic, alicyclic or heterocyclic groups. It can be provided by including a non-polar group such as the first one. Examples of amphiphilic compounds include, but are not limited to, phospholipids, amino lipids, sphingolipids and the like. Representative examples of phospholipids include phosphatidylcholine, phosphatidylethanolamine, phosphatidylserine, phosphatidylinositol, phosphatidic acid, palmitoyloleoylphosphatidylcholine, lysophosphatidylcholine, lysophosphatidylethanolamine, dipalmitoylphosphatidylcholine, dioleoylphosphatidylcholine, distearoylphosphatidylcholine Such as, but not limited to, dilinoleoylphosphatidylcholine. Other compounds that do not contain phosphorus, such as sphingolipids, glycosphingolipid families, diacylglycerols, and β-acyloxyacids also belong to the group designated as amphiphilic lipids. Furthermore, the above-mentioned amphiphilic lipids can be mixed with other lipids including triglycerides and sterols.

  The term “anionic lipid” refers to any lipid that has a negative charge at physiological pH. These lipids include phosphatidylglycerol, cardiolipin, diacylphosphatidylserine, diacylphosphatidic acid, N-dodecanoylphosphatidylethanolamine, N-succinylphosphatidylethanolamine, N-glutarylphosphatidylethanolamine, lysylphosphatidylglycerol, and neutral lipids Other anionic modifying groups bonded to, but not limited thereto.

  The term “cationic lipid” means any of a plurality of lipid species that carry a net positive charge at a selected pH, such as physiological pH. Such lipids include N, N-dioleoyl-N, N-dimethylammonium chloride (“DODAC”), N- (2,3-oleyloxy) propyl-N, N, N-trimethylammonium chloride (“DOTMA”). ), N, N-distearyl-N, N-dimethylammonium bromide (“DDAB”), N- (2,3-oleoyloxy) propyl-N, N, N-trimethylammonium chloride (“DOTAP”), 3 -(N- (N ', N'-dimethylaminoethane) -carbamoyl) cholesterol ("DC-Chol"), and N (1,2-dimyristylprop-3-yl) N, N-dimethylhydroxy Examples include, but are not limited to, ethyl ammonium bromide (“DMRIE”). In addition, several commercial formulations of cationic lipids are available and can be used in the present invention. These include, for example, commercially available cationic liposomes including LIPOFECTIN® (DOTMA and 1,2-dioleoyl-sn-3-phosphoethanolamine (“DOPE”), GIBCO / BRL, Grand Island, New York, USA ), LIPOFECTAMINE® (N- (1- (2,3-oleyloxy) propyl) -N (2- (sperminecarboxamido) ethyl) -N, N-dimethylammonium trifluoroacetic acid (“DOSPA”)) And ("DOPE"), a commercially available cationic liposome containing GIBCO / BRL), and a commercially available ethanol solution of TRANSFECTAM (R) (dioctadecylamidoglycylcarboxyspermine ("DOGS")) Cationic fat , Promega, Madison, Wis., USA), and the like. Lipids that are cationic and positively charged below physiological pH are DODAP, DODMA, DMDMA, and the like.

  “Lipid vesicles” include, but are not limited to, liposomes in which an aqueous volume is encapsulated by an amphiphilic lipid bilayer, or lipids that coat the interior with large molecular components such as plasmids. Refers to any lipid composition that can be used to deliver substances such as liposomes with reduced or lipid aggregates or micelles in which encapsulated components are contained within a relatively disordered lipid mixture.

  As used herein, “lipid encapsulating” means a lipid formulation that provides a compound that is fully encapsulated, partially encapsulated, or both.

  As used herein, the term “SPLP” refers to a stable plasmid lipid particle. SPLP refers to vesicles that contain nucleic acids such as plasmids and coat the interior with reduced aqueous properties.

(II. Overview)
The present invention provides a process and apparatus for producing lipid vesicles. This process includes, but is not limited to, a wide range of products including cationic lipids, anionic lipids, neutral lipids, polyethylene glycol (PEG) lipids, hydrophilic polymer lipids, membrane fusion lipids and sterols. It can be used to produce lipid vesicles carrying lipid components. Hydrophobic actives can be incorporated into organic solvents containing lipids (eg, ethanol), and nucleic acids and hydrophilic activities can be added to the aqueous component. In certain embodiments, the process of the present invention can be used to prepare a microemulsion in which a lipid monolayer surrounds an oil-based nucleus. In certain preferred embodiments, the process and apparatus are used to prepare lipid vesicles, ie, liposomes, and the therapeutic agent is encapsulated within the liposomes upon formation of the liposomes.

(III. Manufacturing process)
FIG. 1 is an example of a representative flowchart 100 for the method of the present invention. This flowchart is merely an illustration and should not limit the scope of the claims herein. Those skilled in the art will recognize other variations, modifications, and changes.

  In one aspect, the method provides a lipid solution 110, such as a clinical grade lipid, that is synthesized under good manufacturing practice (GMP) and then solubilized in an organic solution 120 (eg, ethanol). Similarly, therapeutic agents such as nucleic acid 112 or other agents are prepared under GMP. Thereafter, a therapeutic solution (eg, plasmid DNA) 115 containing a buffer (eg, citrate) is mixed with a lipid solution 120 dissolved in a lower alkanol to form a liposome formulation 130. In a preferred embodiment of the invention, the therapeutic agent is “passively encapsulated” in the liposome simultaneously with the formation of the liposome. However, those skilled in the art will appreciate that the processes and devices of the present invention are equally applicable to active liposome containment or loading after vesicle formation.

  According to the process and apparatus of the present invention, the action of lipid and buffer solution continuously introduced into a mixing environment such as a mixing chamber causes continuous dilution of a lipid solution containing a buffer solution. Liposomes are produced almost instantaneously upon mixing. As used herein, the phrase “continuously diluting a lipid solution containing a buffer” (and variations thereof) generally means that the lipid solution is sufficiently effective to carry out vesicle production, and in the hydration process. Means sufficient and rapid dilution. By mixing the aqueous solution with the organic lipid solution, the organic lipid solution undergoes a continuous stepwise dilution in the presence of a buffer (aqueous) solution to produce liposomes.

  In the process of the present invention, the organic lipid solution preferably contains an organic solvent such as a lower alkanol. In one embodiment, the liposome is then diluted 140 with a buffer (eg, citrate) to increase nucleic acid (eg, plasmid) uptake. Prior to sample concentration 160, free therapeutic agent (eg, nucleic acid) is removed 150 using, for example, an anion exchange cartridge. In addition, the sample is concentrated (eg, about 0.9 mg / mL plasmid DNA) by using ultrafiltration step 170 to remove alkanol, alkanol is removed, and the buffer is further replaced with alternative buffer. Replace 180 with solution (eg, including saline buffer). The sample is then filtered 190 and placed in a vial 195. This process will now be described in more detail below using the steps shown in FIG.

(1. Solubilization of lipids and dissolution of therapeutic agents)
In one embodiment, the liposome vesicles of the present process are stable plasmid lipid particle (ie SPLP) formulations. Those skilled in the art will appreciate that the following description is for illustrative purposes only. The process of the present invention is applicable to a wide range of lipid vesicle types and sizes. These lipid vesicles include not only multilayer lipid vesicles (MLV) but also single bilayer lipid vesicles known as monolayer lipid vesicles capable of forming small (SUV) and large (LUV). There is, but is not limited to this. In addition, vesicles include micelles, lipid nucleic acid particles, virosomes, or the like. One skilled in the art will appreciate that the process and apparatus of the present invention is suitable for other lipid vesicles.

  The preferred size of liposomes produced according to the process and apparatus is about 50-550 nm in diameter. In certain preferred embodiments, the size distribution of the liposome formulation has an average size (eg, diameter) of about 70 nm to about 300 nm, more preferably an average size of less than about 200 nm, such as about 150 nm or less (eg, about 100 nm). .

  In one embodiment, the liposome formulation (eg, SPLP formulation) of the present invention includes four lipid components: phospholipid, cholesterol, PEG lipid, and cationic lipid. In a preferred embodiment, the phospholipid is DSPC, the PEG lipid is PEG-DSG, and the cationic lipid is DODMA. In a preferred embodiment, the molar composition is approximately 20: 45: 10: 25 = DSPC: Chol: PEG-DSG: DODMA. In certain embodiments, the organic solvent concentration at which the lipid is soluble is from about 45% v / v to about 90% v / v. In certain preferred embodiments, the organic solvent is a lower alkanol. Preferred lower alkanols include, but are not limited to, methanol, ethanol, propanol, butanol, pentanol, isomers thereof, and combinations thereof. In one embodiment, the solvent is preferably about 50-90% v / v ethanol. The lipid preferably occupies a volume of about 1 mL / g to about 5 mL / g.

  The lipid is solubilized 120 using, for example, a moderate temperature overhead stirrer. In one embodiment, the total lipid concentration of this solution is about 15.1 mg / mL (20 mM). In certain preferred embodiments, the therapeutic agent (eg, nucleic acid) is contained in an aqueous solution (eg, a buffer) and diluted to a final concentration. In a preferred embodiment, for example, the final concentration is about 0.9 mg / mL in a citrate buffer having a pH of about 4.0. In this case, the volume of the plasmid solution is the same as the alkanol lipid solution. In one embodiment, the therapeutic (eg, nucleic acid) solution is prepared in a jacketed stainless steel container equipped with an overhead mixer. In some cases, the temperature is the same as the lipid solution at the time prior to lipid vesicle formation, but it is not necessary to heat the sample for preparation.

  In one embodiment, the therapeutic agent is incorporated into the lipid solution. In certain preferred embodiments, the therapeutic agent in the lipid solution is lipophilic. Preferred lipophilic drugs include, for example, Protax III and paclitaxol, lipophilic benzoporphyrin, verteporfin, a lipid prodrug of Foscarnet, 1-O-octadecyl-sn-glycerin-3-phosphonoform Mate (ODG-PFA), dioleoyl [3H] iododeoxyuridine ([3H] IDU-O12), iBOC [-L-Phe]-[D-beta-Nal] -Pip- [α- (OH) -Leu] There are taxols, taxol derivatives, etc., including lipid derivatized HIV proteolytic enzyme inhibitory peptides such as -Val (7194), and other lipid derivatizing drugs or prodrugs.

(2. Liposome formation)
After preparing a solution, such as a lipid solution 120 and an aqueous therapeutic (eg, nucleic acid) solution 115, they are mixed 130 together, for example, using a peristaltic pump mixer. In some embodiments, pumps are introduced at substantially equal flow rates within the mixing environment. In some embodiments, the mixing environment comprises a “T” connector or mixing chamber. In this case, the fluid lines, and thus the fluid flow, preferably meet at a narrow opening in the “T” connector with flows that are about 180 ° opposite to each other. Other relative introduction angles may be used, for example, between 27 ° and 90 °, and between 90 ° and 180 °. Lipid vesicles are formed substantially instantaneously as the solution flows merge and mix within the mixing environment. Lipid vesicles are formed when an organic solution containing dissolved lipids and an aqueous solution (eg, a buffer) is simultaneously and continuously mixed. Conveniently and surprisingly, by mixing the aqueous solution with the organic lipid solution, the organic lipid solution undergoes a continuous stepwise dilution to produce liposomes substantially instantaneously. The pump mechanism can be configured to deliver equal or different lipid and aqueous solution flow rates in a mixed environment that creates lipid vesicles in a high alkanol environment.

  Conveniently and surprisingly, the process and apparatus for mixing lipid solutions and aqueous solutions taught herein is about the same as the formation of liposomes in the formed liposomes at about the same time. Provide encapsulation of therapeutic agents with encapsulation efficiency up to 90%. If necessary, other processing steps described herein can be used to further improve encapsulation efficiency and concentration.

  In a preferred embodiment, the process and apparatus of the present invention can be used to instantly form lipid vesicles in a fully scalable continuous two-step process. In one embodiment, lipid vesicles with an average diameter of less than about 200 nm are formed that do not need to be further reduced in size by high energy processes such as membrane extrusion, sonication, or microfluidization.

  In one embodiment, lipid vesicles are formed when a lipid dissolved in an organic solvent (eg, ethanol) is mixed with an aqueous solution (eg, buffer) when diluted in stages. This controlled graded dilution is achieved by mixing the aqueous and lipid streams together in an opening such as a T-connector. The lipid, solvent and solute concentrations thus obtained can be kept constant throughout the vesicle formation process.

  One embodiment of the process of the present invention is shown in FIG. In one embodiment, vesicles are prepared using a process of the invention by two-stage serial dilution without gradients. For example, the initial serial dilution forms vesicles in a high alkanol (eg, ethanol) environment (eg, about 30% to about 50% v / v ethanol). Subsequently, these vesicles are stabilized by gradually reducing the alkanol (eg, ethanol) concentration from about 17% v / v to about 25% v / v or less to about 25% v / v or less. Can do. In preferred embodiments, the therapeutic agent present in the aqueous solution or lipid solution encapsulates the therapeutic agent upon liposome formation.

  As shown in FIG. 2, in one embodiment, the lipid is initially from about 40% v / v to about 90% v / v, more preferably from about 65% to about 90% v / v, most preferably about It is dissolved in an alkanol environment from 80% v / v to about 90% v / v (A). The lipid solution is then diluted stepwise by mixing with an aqueous solution to form vesicles at an alkanol (eg, ethanol) concentration of about 37.5-50% (B). By mixing the aqueous solution with the organic lipid solution, the organic lipid solution undergoes serial stepwise dilution to produce liposomes. Furthermore, lipid vesicles such as SPLP (lipid particles) can be stabilized by further serial dilution of the vesicles to an alkanol concentration of about 25% or less, preferably about 19-25% (C).

  In some embodiments, for both serial dilutions (A → B and B → C), the resulting ethanol, lipid, and solute concentrations are kept at a constant level in the receiving vessel. At these higher ethanol concentrations, the initial mixing step continues, but rearrangement of lipid monomers into the bilayer proceeds in a more orderly manner compared to vesicles formed by dilution at lower ethanol concentrations. To do. The mechanism is unknown, but these higher ethanol concentrations are thought to promote nucleic acid association by cationic lipids in the bilayer. In a preferred embodiment, nucleic acid encapsulation occurs within a range of alkanol (eg, ethanol) concentrations of 22% or greater.

  In some embodiments, after the lipid vesicles are formed, they are collected in another container, such as a stainless steel container. In one aspect, lipid vesicles are formed at a rate of about 60 to about 80 mL / min. In one aspect, after the mixing step 130, the lipid concentration is about 1-10 mg / mL and the therapeutic agent (eg, plasmid DNA) concentration is about 0.1-3 mg / mL. In certain preferred embodiments, the lipid concentration is about 7.0 mg / mL and the therapeutic agent (eg, plasmid DNA) concentration is about 0.4 mg / mL, giving a DNA: lipid ratio of about 0.06 mg / mg. The buffer concentration is about 1-3 mM and the alkanol concentration is about 45% v / v to about 90% v / v. In a preferred embodiment, the buffer concentration is about 3 mM and the alkanol concentration is about 45% v / v to about 60% v / v.

(3. Liposome dilution)
Returning to FIG. 1, if the lipid vesicle suspension is optionally diluted 140 after the mixing step 130 and prior to removal of the free plasmid, the therapeutic (eg, nucleic acid) encapsulation can be enhanced. it can. For example, if the therapeutic agent encapsulation is about 30-40% before the dilution step 140, it can be increased to about 70-80% after the incubation after the dilution step 140. In step 140, the liposome formulation is about 10% to about 40% alkanol, preferably about 20 by mixing with an aqueous solution such as a buffer (eg, citrate buffer, 100 mM NaCl, 1: 1, pH 4.0). Dilute to% alkanol. Such further dilution is preferably achieved with a buffer. In some embodiments, such further diluted liposome solution is a serial stepwise dilution. The diluted sample may then optionally be incubated at room temperature.

(4. Removal of free therapeutic agents)
After the optional dilution step 140, about 70-80% or more of the therapeutic agent (eg, nucleic acid) is entrapped within the lipid vesicle (eg, SPLP) and free therapeutic agent can be removed from the formulation 150. . In some embodiments, anion exchange chromatography is used. Conveniently, the use of an anion exchange resin that exhibits a high dynamic nucleic acid removal capability is disposable, may be pre-sterilized and validated, and is fully scalable. In addition, this method favors removal of free therapeutic agents (eg, nucleic acids such as 25% total plasmid). The sample volume after chromatography is unchanged and the therapeutic (eg, nucleic acid) and lipid concentrations are about 0.64 and 14.4 mg / mL, respectively. At this point, the sample can be analyzed for encapsulated therapeutics and adjusted to about 0.55 mg / mL.

(5. Sample concentration)
In some cases, for example, using ultrafiltration 160 (eg, parallel flow dialysis), the liposome solution is optionally concentrated about 2-6 times, preferably about 4 times. In one embodiment, the sample is transferred to the ultrafiltration system supply reservoir and the buffer is removed. Various processes such as ultrafiltration can be used to remove the buffer. In one embodiment, the buffer is removed using a cartridge filled with polysulfone hollow fibers having, for example, an internal diameter of about 0.5 mm and a nominal molecular weight cut-off value (NMWC) of 30,000. Liposomes are retained within this hollow fiber and recirculated until the solvent and small molecules are removed from the formulation by passing through the pores of the hollow fiber. In this procedure, the filtrate is known as the osmotic solution. When the concentration step is complete, the therapeutic (eg, nucleic acid) and lipid concentrations increase to about 0.90 and 15.14 mg / mL, respectively. In one embodiment, the alkanol concentration remains unchanged, but the alkanol: lipid ratio is reduced by a factor of four.

(6. Removal of alkanol)
In one embodiment, the concentrated formulation is then subjected to about 5-15 parts, preferably about 10 parts of an aqueous solution (eg, buffer) (eg, citrate buffer pH 4.0) to remove alkanol 170. (25 mM citrate, 100 mM NaCl) is diafiltered, alkanol concentration is less than about 1% at the completion of step 170. Lipid and therapeutic (eg, nucleic acid) concentrations are unchanged and treatment It is preferable to maintain a constant value for the drug encapsulation level.

(7. Buffer replacement)
After removal of the alkanol, the aqueous solution (eg, buffer) is subsequently diafiltered against another buffer 180 (eg, 10 parts saline, 150 mM NaCl, pH 7.4 containing 10 mM Hepes), Replaced. Preferably, the concentration ratio of lipid to therapeutic agent (eg, nucleic acid) remains unchanged, and the level of unchanged and nucleic acid encapsulation is constant. In some cases, sample yield can be improved by flushing the cartridge with buffer in a concentrated sample of about 10% volume. In some embodiments, this rinse is then added to the concentrated sample.

(8. Aseptic filtration)
In certain preferred embodiments, aseptic filtration 190 of the sample can optionally be performed at a lipid concentration of about 12-14 mg / mL. In some embodiments, filtration is performed at a pressure of less than about 40 psi using a pressure controlled dispensing container with a capsule filter and a beating jacket. Slightly heating the sample may improve the ease of filtration.

(9. Aseptic filling)
Aseptic filling step 195 is performed using a process similar to conventional liposomal formulations. The process of the present invention results in about 50-60% of the therapeutic agent (eg, nucleic acid) introduced into the final product. In certain preferred embodiments, the final product has a therapeutic to lipid ratio of approximately 0.04 to 0.07.

(IV. Therapeutic)
The lipid-based pharmaceutical formulations and compositions of the present invention are useful for systemic or local delivery of therapeutic or bioactive agents and are also useful for diagnostic assays. The following description will generally refer to liposomes, but one of ordinary skill in the art will readily appreciate that this content is fully applicable to other drug delivery systems of the present invention.

  As described above, the therapeutic agent is preferably incorporated into lipid vesicles during vesicle formation. In one embodiment, hydrophobic activity can be incorporated into an organic solvent containing lipids, while nucleic acids and hydrophilic activity can be added to the aqueous component. In some cases, the therapeutic agent includes one of the proteins, nucleic acid, antisense nucleic acid, ribozyme, tRNA, snRNA, siRNA, pre-concentrated DNA, antigen, and combinations thereof. In a preferred embodiment, the therapeutic agent is a nucleic acid. Nucleic acids include, for example, herpes simplex virus, thymidine kinase (HSV-TK), cytosine deaminase, xanthine-guanine phosphoribosyltransferase, p53, purine nucleoside phosphorylase, carboxyesterase, deoxycytidine kinase, nitroreductase, thymidine phosphorylase Alternatively, it encodes a protein such as cytochrome P450 2B1.

  In certain embodiments, the therapeutic agent is incorporated into the organic lipid component. In some cases, the therapeutic agent is lipophilic. Preferred lipophilic agents include, for example, Protax III and Paclitaxol, lipophilic benzoporphyrin, verteporfin, a lipid prodrug of Foscarnet, 1-O-octadecyl-sn-glycerin-3 -Phosphonoformate (ODG-PFA), dioleoyl [3H] iododeoxyuridine ([3H] IDU-O12), iBOC [-L-Phe]-[D-beta-Nal] -Pip- [α- (OH ) -Leu] -Val (7194) and other lipid derivatized HIV proteolytic enzyme inhibitory peptides, and other lipid derivatized drugs or prodrugs, and the like.

  In another embodiment, the lipid vesicles of the invention can introduce one or more therapeutic agents after vesicle formation. In certain embodiments, the therapeutic agent treated using the present invention can be any of a variety of agents selected as an appropriate treatment for the disease to be treated. Often the drug is an antineoplastic agent such as vincristine, doxorubicin, mitoxantrone, camptothecin, cisplatin, bleomycin, cyclophosphamide, methotrexate, streptozotocin and the like. In particular, anticancer drugs include actinomycin D, vincristine, vinblastine, cystine arabinoside, anthracyclines, alkylating agents, platinum compounds, antimetabolites, and, for example, methotrexate and analogs of purines and pyrimidines. It is preferred to include nucleoside analogs. Furthermore, it may be preferable to deliver anti-infectious agents to specific tissues by this process. The composition of the present invention is not limited thereto, but includes local anesthetics such as dibucaine, chlorpromazine; beta-receptor blockers such as propranolol, timolol, labetolol; antihypertensive agents such as clonidine, hydralazine; Depressants, eg: imipramine, amitriptyline, doxepim; anti-convertants, eg: phenytoin; antihistamines, eg: diphenhydramine, chlorpheniramine, promethazine; antibiotics / antibacterials, eg: gentamicin, ciprof Loxacin, cefoxitin; antifungal agents, eg, miconazole, terconazole, econazole, isoconazole, butaconazole, clotrimazole, Traconazole, nystatin, naphthifine, and amphotericin B; other drugs such as anthelmintics, hormones, hormone antagonists, immunomodulators, neurotransmitter antagonists, glaucoma therapeutics, vitamins, narcotics, and imaging agents Can be used for selective delivery of.

(V. Device)
In another embodiment, the present invention provides an apparatus for performing the process of the present invention. FIG. 3 is an exemplary schematic diagram of an apparatus 300 according to an embodiment of the present invention. This schematic diagram is merely an illustration, and does not limit the scope of the claims of this specification. Those skilled in the art will recognize other variations, modifications, and changes.

  In one embodiment, the apparatus of the present invention includes two reservoirs, an aqueous solution reservoir 310 and an organic solution reservoir 320 to hold an aqueous solution and an organic solution, respectively. In certain embodiments, lipid vesicle formulations are prepared rapidly at low pressure (eg, <10 psi), and the devices and processes of the present invention are fully scalable (eg, 0.5 mL-5000 L). On the 1 L scale, lipid vesicles are formed at about 0.4-0.8 L / min. In certain preferred embodiments, the apparatus does not use a static mixer or a dedicated extrusion apparatus.

  In one embodiment, the mixing chamber 340 is a T-connector and has an optional hose projection where the liquid lines 334 and 336 collide with each other at 180 °. The mixing angle can also be varied, and lipid vesicles of less than about 100 nm can be formed between angles of about 27 ° to about 90 °, or between 90 ° and 180 °. In a preferred embodiment, lipid vesicles having a well-normalized and reproducible mean diameter are prepared using substantially equal flow rates in the flow line. In other embodiments, well-defined and reproducible mean diameter lipid vesicles are prepared, for example, by varying the flow rate of the liquid line to ensure adequate mixing. In a preferred embodiment, the variation between flow rates is less than 50%, more preferably less than about 25%, more preferably less than about 5%.

  FIG. 13 shows a T-connector and associated flow dynamics according to one embodiment. An example flow rate and the resulting shear rate and Reynolds number (turbulent flow measurement) are shown in FIG. 14 and are described in more detail in Example 8 thereafter. Compared to previous systems, the present invention provides non-turbulent flow and increased shear rate at a much lower (and substantially equivalent) flow rate. For example, the present invention provides non-turbulent flow in a mixed environment with shear rates between about 500 / s and 3300 / s at flow rates between about 0.075 and about 0.3 L / min (both flow lines). Nre <2000) is conveniently provided.

  The mixing of the two types of liquid components can be carried out, for example, using a peristaltic pump 330, a displacement pump, or pressurization of both lipid ethanol and buffer containers 320 and 310. In one aspect, a Watson-Marlow 505Di / L pump with a 505L pump head is used and a silicone tube material (eg, cured platinum with ID 3.2 mm, wall thickness 2.4 mm, catalog number 913A032024). As available from Watson Marlow as a flow line in polypropylene or stainless steel T connectors (eg 1/8 "ID). Lipid vesicles are generally formed at room temperature, but lipid vesicles are In accordance with the present invention, it may be formed at elevated temperatures, and unlike other existing approaches, a buffer composition is generally not required.In practice, the process and apparatus of the present invention converts the lipid in the alkanol to water. In some embodiments, lipid vesicles can be formulated by mixing. Process and apparatus for forming a lipid vesicle is less than the diameter 200 nm.

  When lipid vesicles containing plasmid DNA (such as SPLP) are prepared, the ratio of the plasmid to cationic lipid and counterion can be optimized. For purified formulations, a 70-95% plasmid DNA (“pDNA”) encapsulation and ethanol removal step after mixing is preferred. The pDNA encapsulation level can be increased by diluting this initial SPLP formulation. Surprisingly, the process and apparatus of the present invention provides an encapsulation efficiency of up to about 90% by mixing a solution in a mixed environment (one of the solution components includes a therapeutic agent).

  In one embodiment, the liposome production apparatus 300 of the present invention further includes a temperature adjustment mechanism (not shown) for temperature control of the reservoirs 310 and 320. The liquid from the first storage unit 310 and the second storage unit 320 flows into the mixing chamber 340 at the same time through the separation opening. The apparatus 300 further includes a collection reservoir 350 for collecting liposomes downstream of the mixing chamber. Further, in certain aspects, the apparatus 300 further comprises a storage container upstream of one or both of the reservoirs 310 and 320. Further, one or both of the reservoirs 310 and 320 are preferably jacketed stainless steel containers equipped with an overhead mixer.

  In another embodiment, the present invention provides an apparatus having an ultrafiltration system for performing the process of the present invention. FIG. 4 is a representative illustrative example of an apparatus 400 according to one embodiment of the present invention. This schematic diagram is merely an illustration, and does not limit the scope of the claims of this specification. Those skilled in the art will recognize other variations, modifications, and changes.

  In some embodiments, the apparatus 400 includes a number of reservoirs and is equipped with an ultrafiltration system. The aqueous solution reservoir 440 and the organic solution reservoir 430 have preparation vesicles 433 and 425, respectively, upstream. In one embodiment, the lipid preparation container 425 optionally comprises a lipid preparation container and an alkanol storage container 421 in liquid flow.

  As shown in FIG. 4, the ultrafiltration system has an incubation vessel 450 in liquid communication comprising a collection vessel 455, an exchange column 460, and a tangential flow ultrafiltration cartridge 465. The ultrafiltration system optionally includes a permeation vessel 470. In certain embodiments, ultrafiltration is used to concentrate the SPLP sample and subsequently remove ethanol from the formulation by buffer replacement.

  In one embodiment of the operation, the diluted SPLP is transferred to the ultrafiltration system supply reservoir. For example, concentration is performed by removing the buffer solution and ethanol using a cross flow cartridge 465 filled with polysulfone hollow fibers having an inner diameter of about 0.5 mm and a 100,000 molecular weight cut-off value (MWCO). The SPLP is retained in the hollow fiber and recycled. On the other hand, ethanol and buffer components are removed from the formulation by passing through the pores of these hollow fibers. This filtrate is known as the permeate and is discarded by the container 470. After the SPLP is concentrated to the desired plasmid concentration, the buffer in which the SPLP is suspended is removed by ultrafiltration and replaced with an equal volume of final buffer. Ultrafiltration can be replaced with other methods such as normal dialysis.

VI. Example (Example)
This example demonstrates various physical and chemical properties of SPLPs produced according to one embodiment of the present invention.

  Table I: Ethanol, pDNA content and lipid content in process steps according to the invention

* Estimate 10% total volume and SPLP loss after buffer replacement step.
** Assume that 75% of the pDNA is encapsulated and all free DNA has been removed. Estimate 5% loss of SPLP on anion exchange cartridge. In this step, the sample is analyzed for encapsulated pDNA and 0.55 mg / ml to predict SPLP loss during the filtration step (the adjusted concentration is shown in parentheses for 0.55 mg / ml pDNA). adjusted to ml.
*** Assumes maximum 5% capacity loss and total SPLP loss up to 10%.

  Table II shows the specifications for the plasmids produced according to one embodiment of the present invention.

  Table III shows the SPLP specifications made according to one aspect of the present invention.

(Example 2)
This example illustrates various process parameters in one embodiment of the present invention.

  In one embodiment of SPLP, a sufficiently high ethanol concentration is provided so that none of the individual lipid components precipitate, so even if the initial ethanol concentration changes due to lipid lysis, the vesicle size or There was little effect on any of the DNA encapsulation (see FIG. 5). Below 75% ethanol, lipids did not dissolve when heated to 55 ° C. Lipids dissolved in 75% ethanol at 55 ° C. formed SPLP with a larger average diameter and lower DNA encapsulation (see FIG. 5).

  The initial DNA to lipid ratio varied from 0.048 to 0.081 mg DNA: mg lipid formulation, and similarly sized vesicles with 77-90% DNA encapsulation were formed.

  SPLPS was prepared in the initial mixing step at a pH range of about 3.5-6 and all formulations had an average particle size of less than 150 nm and showed DNA encapsulation efficiency above 50%. (See FIG. 6). Although it is possible to prepare vesicles of similar vesicle size at higher pH, the DNA encapsulation efficiency is low.

  In certain embodiments, the average vesicle size of empty vesicles prepared using one of the processes of the present invention is the salt concentration of the buffer to be diluted (eg, sphingomyelin: cholesterol cholesterol vesicles, EPC: EPG vesicles). Changing the ionic conditions in the buffer affects the tendency of a given lipid to align itself within the bilayer and vesicles.

  During the development of certain SPLP formulations, it was found that both the pH and salt concentration of the dilution buffer had a significant effect on DNA encapsulation efficiency. Inevitably, the dilution buffer for the cationic lipid component (DODMA) with a pH value lower than pKa showed higher encapsulation values (FIG. 7). Interestingly, a final salt concentration of 150 mM was also optimal for DNA encapsulation (FIG. 8).

(Example 3)
This example illustrates the use of one process of the present invention to produce EPC and POPC vesicles.

  POPC vesicles are useful as “sink” vesicles for membrane fusion assays. In particular, by using them in excess, PEG lipids can be removed from other liposomes, thus destabilizing other liposomes and fusing them with the desired membrane. EPC vesicles are useful for removing cholesterol from arterial plaques.

  Vesicles were prepared with 80% initial ethanol concentration and 10 mM lipid concentration. After mixing and dilution, the ethanol concentration was 20% and the lipid concentration was 5 mM. The EPC formulation was mixed with PBS and diluted, and POPC was mixed with HBS and diluted. Both formulations were concentrated and ethanol was removed using an ultrafiltration cartridge, ie EPC against PBS, and POPC against HBS. Subsequently, both formulations were sterile filtered using a 0.22 um syringe filter.

Example 4
This example demonstrates the use of one process of the present invention to produce EPC / cholesterol vesicles with a pH gradient.

  Monolayered lipid vesicles (LUV) containing EPC and cholesterol are generally produced by hydrating lipid films and forming multilamellar lipid vesicles (MLV) that undergo vesicle size reduction by using high pressure extrusion. Has been prepared. It is well known that these vesicles can be prepared by an acidic aqueous interior and a pH gradient across the lipid bilayer. It was shown that weakly basic lipophilic molecules accumulate in these vesicles at high internal concentrations. Various drug-introduced liposomes currently in late clinical trials utilize this approach (eg, myosets: doxorubicin-introduced vesicles).

  In one aspect, safranin is used to determine if a pH gradient or the like is present. Safranin is a lipophilic basic dye used to test membrane pH gradients.

  EPC / Chol vesicles were prepared using this process and apparatus at 80% initial ethanol concentration and 10 mM lipid concentration (see FIGS. 9A-B). After mixing and dilution, the ethanol concentration was 20% and the lipid concentration was 5 mM. Three different formulations were prepared:

  1. Formulation mixed and diluted with PBS (control group).

  2. Formulation mixed and diluted with 150 mM citrate (final citrate concentration is 94 mM).

  3. Formulation mixed and diluted with 300 mM citrate (final citrate concentration is 188 mM).

  After mixing and dilution, each sample was concentrated and the ethanol was removed using ultrafiltration. After the concentration step, each sample was diafiltered with its dilution buffer so that the acidic citrate buffer present in the vesicles did not leak during ethanol removal. All samples were finally formulated with phosphate buffered saline external buffer at pH 7.4. After sterile filtration, the average vesicle size of these formulations was very uniform (90-92 nm), showing acceptable standard deviations and chi-square values (Table V).

  Following dialysis, lipid concentrations were analyzed for vesicles using an infinite cholesterol assay. Subsequently, a solution containing 5 mM lipid and 0.2 mM safranin obtained from the filtered 10 mM stock solution was prepared. This solution was incubated at 37 ° C. for 30 minutes. Subsequently, a 500 ul aliquot of each incubation solution was passed through a 2-mL Sepharose CL4B gel filtration column. The free dye was separated from the vesicles and the fraction containing lipids was collected and analyzed. Safranin concentration was quantified by measuring the fluorescence of the sample with 516 nm excitation and 585 nm emission.

  Vesicles with an acidic interior showed the highest encapsulation with safranin accumulated along with 94 mM citrate-containing vesicles. In contrast, PBS control vesicles were encapsulated with very little safranin. 188 mM citrate vesicles also encapsulated some safranin, but not as much as 94 mM citrate vesicles (see FIG. 10).

(Example 5)
This example demonstrates the use of one process of the present invention to produce sphingomyelin / cholesterol vesicles.

  Sphingomyelin / cholesterol vesicles are preferred due to their durability and strength. These vesicles can also be used to encapsulate drugs using a pH gradient. However, these LUVs generally need to be formed at temperatures above 65 ° C., and high pressure extrusion is used. In order to form these vesicles with a lipomixer, several variables need to be considered, such as ethanol concentration, lipid concentration, and salt concentration of the mixing / dilution buffer.

  The vesicles were formulated with a 55/45 SM / Chol (mol: mol) ratio, while the initial ethanol concentration after mixing varied between 50 and 25%. The dilution buffer tested included PBS, water, 10 mM citrate, 150 mM citrate, and 300 mM citrate. The final lipid concentration ranged from 0.5 to 2.5 mM. The vesicles formulated in the presence of salt (ie, using buffer) were 200-500 nm showing MLV. Aliquots of these samples were dialyzed against both 150 mM citrate and water to remove ethanol and stabilize the vesicles.

(Example 6)
This example demonstrates the use of one process of the present invention to prepare vesicles that passively encapsulate small molecules such as calcein.

  Calcein is a fluorescent dye that self-quens at concentrations above 10 mM. Calcein encapsulated vesicles can be used in fusion assays to determine if the vesicles have fused together. Fusion reduces the internal calcein concentration, resulting in fluorescence. After mixing and dilution, vesicles were prepared with DSPC: CHOL: PEG DLG: DODMA (20: 55: 10: 15) at 19% ethanol concentration and 2 mM lipid (see FIG. 11). Lipids dissolved in ethanol were mixed with a solution containing 20 mM citrate and 75 mM calcein, and the resulting vesicles were subsequently diluted with 300 mM NaCl and 37.5 mM calcein. Calcein was obtained from a 100 mM stock solution. The final calcein concentration in the vesicle was 37.5 mM.

  After mixing and dilution, the vesicles were dialyzed overnight against HBS to remove unencapsulated dye. The vesicle was passed through a gel filtration column because it failed to remove all of the free dye. The lipid fraction was collected and analyzed. Indeed, calcein was found to be self-quenched at concentrations inside the vesicles. This is clear evidence that the process and apparatus of the present invention can be used to prepare vesicles that passively encapsulate small molecules.

(Example 7)
This example illustrates the use of one process of the present invention over a conventional method.

  Referring to FIG. 12, lipids are dissolved in 90% ethanol (A) and using the apparatus of the present invention, 45% (B) and 22.5% ethanol as indicated by the solid line (“Lipomixer LipoMixer”). Dilute by either stepwise until (C) or by continuously dropping to a final ethanol concentration of 22.5% (C) in a stirred buffer as indicated by the dotted line. It was. Although the final ethanol concentration in both formulations was the same, the SPLP formed by the process of the present invention had 85% DNA encapsulation. In contrast, vesicles prepared by ethanol instillation had only 5% DNA encapsulation.

(Example 8)
This example demonstrates various conditions and properties for forming liposomes according to the present invention. It should be appreciated that other conditions and parameters may be used and that the ones used here are only examples.

  In FIGS. 13 and 14, various flow rates (both lipid and aqueous solution flow rates are substantially equivalent) are modeled and analyzed to reveal various parameters such as shear rate, Reynolds number (Nre) and vesicle size. went. Parameters and conditions were measured at the outlet of the T-connector that corrects the density and viscosity of the resulting ethanol solution. Neither the extra turbulence resulting from the two flows meeting each other nor the extra turbulence resulting from the flow turning at a 90 degree corner contributed.

  The examples and embodiments described herein are illustrative only, and various modifications and changes made in light of the examples and embodiments are included in the specification and appended claims. It should be. All publications, patents and patent applications cited herein are hereby incorporated by reference in their entirety.

FIG. 1 shows a flowchart for a manufacturing process according to an embodiment of the invention. FIG. 2 shows a schematic diagram of a process for producing liposomes in one embodiment of the present invention. FIG. 3 shows a schematic diagram of an apparatus according to an embodiment of the invention. FIG. 4 shows a schematic diagram of an apparatus comprising an ultrafiltration system according to an embodiment of the present invention. FIG. 5 shows the effect of changes in ethanol concentration of the initial lipid solution on SPLP mean diameter and DNA encapsulation. DNA encapsulation efficiency and vesicle size were measured after the dilution step. FIG. 6 shows the effect of changes in pH of the initial plasmid solution on SPLP mean diameter and DNA encapsulation. DNA encapsulation efficiency and vesicle size were measured after the dilution step. FIG. 7 shows the effect of pH change of the buffer used in the dilution step on pDNA encapsulation efficiency. FIG. 8 shows the effect of changing the salt concentration of the buffer used in the dilution step on the pDNA encapsulation efficiency. FIG. 9A shows a schematic diagram of the process for producing the liposomes of the present invention. FIG. 9B shows a schematic diagram of a process for producing the liposomes of the present invention. FIG. 10 shows the encapsulation of safranin in certain liposomes of the present invention. FIG. 11 shows a schematic diagram of a process for producing the liposome of the present invention. FIG. 12 shows a comparison between one embodiment of the present invention for pDNA encapsulation and the ethanol dropping method. FIG. 13 illustrates a T connector and associated flow dynamics according to one embodiment. FIG. 14 shows various parameters related to the flow in the T-connector of FIG.

Claims (62)

A process for producing lipid vesicles encapsulating a therapeutic agent, the process comprising:
Providing an aqueous solution to the first reservoir;
Providing an organic lipid solution to a second reservoir , wherein one of the aqueous solution and the organic lipid solution comprises a therapeutic agent;
Mixing the aqueous solution with the organic lipid solution, the method comprising mixing the organic lipid solution with the aqueous solution to produce lipid vesicles encapsulating a therapeutic agent ,
Said mixing step comprises introducing said aqueous solution and said organic lipid solution into a mixing environment at equal flow rates; and
The mixed environment includes a T-connector, and the aqueous solution and the organic lipid solution are introduced into the T-connector as a flow opposite to each other by 180 °;
process. The process of claim 1 present in the solution in which the lipid vesicles with an organic solvent concentration of 2 0% v / v or et 5 0% v / v. The process of claim 2, further comprising further diluting the lipid vesicles solution. The process of claim 3, wherein the additional dilution is performed with a buffer. The process of claim 3 wherein the additional diluent is continuous stepwise dilution for diluting the lipid vesicles solution. The lipid vesicle solution A process according to claim 3 having an organic solvent concentration of less than 2 5% v / v after dilution. The process of claim 2 further comprising the step of removing the organic solvent associated with the lipid vesicles solution to form a final form. The process of claim 1 wherein the organic lipid solution comprises an organic solvent. The process of claim 8, wherein the organic solvent is a lower alcohol. The process of claim 8, wherein the organic solvent comprises water. The process of claim 1, wherein the aqueous solution comprises an organic solution. The process of claim 1, wherein the aqueous solution comprises a buffer. The process of claim 1 wherein the lipid vesicle is less than diameter 2 nm. The process of claim 1 wherein said lipid vesicles are formed at 6 0 to 8 0 mL / min. The process of claim 1, wherein the aqueous solution comprises a therapeutic agent. 16. The process of claim 15, wherein the therapeutic agent is selected from the group consisting of protein, plasmid, nucleic acid, antisense nucleic acid, ribozyme, tRNA, snRNA, siRNA, pre-concentrated DNA, and antigen. The process of claim 15, wherein the therapeutic agent is a nucleic acid. The nucleic acid is herpes simplex virus thymidine kinase (HSV-TK), cytosine deaminase, xanthine-guanine phosphoribosyltransferase, p53, purine nucleoside phosphorylase, carboxylesterase, deoxycytidine kinase, nitroreductase, thymidine phosphorylase and cytochrome P450. The process according to claim 17, which encodes a protein selected from the group consisting of 2B1. The process of claim 1, wherein the therapeutic agent is a charged species. The process of claim 1, wherein the organic lipid solution comprises a therapeutic agent. 21. The process of claim 20, wherein the therapeutic agent is lipophilic. 23. The process of claim 21, wherein the lipophilic formulation is selected from the group consisting of Protax III, paclitaxol, taxol, taxol derivatives, and lipid derivatized prodrugs. The process of claim 1, wherein one or both of the first and second reservoirs are temperature controlled. The process of claim 1, wherein one or both of the first and second reservoirs includes a jacketed stainless steel vessel with an overhead mixer. The process according to claim 1, wherein during mixing, the organic lipid solution is serially diluted in the presence of the aqueous solution. The lipid vesicles are 3 . 5 or et al 8. The process of claim 17 present in a solution having a pH of zero. 18. The process of claim 17 , wherein the lipid vesicle has a nucleic acid encapsulation efficiency greater than 50%. 18. The process of claim 17 , wherein the lipid vesicle has a nucleic acid encapsulation efficiency between 80% and 90 %. The process according to claim 17 , wherein the lipid vesicle has a diameter of 150 nm or less. The process of claim 17 wherein the lipid vesicles are present in a solution having a salt concentration of 1 100 mM or et 2 100 mM. Wherein the organic lipid solution comprises an organic solvent concentration of the 70% during the second reservoir v / v or al 1 00% v / v, The process of claim 1. A process according to claim 31, wherein the organic lipid solution during mixing is continuously stepwise diluted to 3 5% v / v or et 5 0% v / v organic solvent concentration. 32. The process of claim 31 , wherein the therapeutic agent is one of an anionic species and a cationic species. An apparatus for producing lipid vesicles encapsulating a therapeutic agent,
A first reservoir for holding an aqueous solution;
A second reservoir for holding an organic lipid solution, one of the aqueous solution and the organic lipid solution comprising a therapeutic agent;
A pump mechanism configured at equal correct flow rate to pump the aqueous solution and the organic lipid solution to the mixed area,
Wherein the organic lipid solution mixes with said aqueous solution in the mixing region, therapeutic agents shi shape forming the encapsulated lipid vesicle; and
The mixed environment includes a T-connector, and the aqueous solution and the organic lipid solution are introduced into the T-connector as a flow opposite to each other by 180 °;
apparatus. 35. The device of claim 34 , further comprising a receiving container for receiving a therapeutic agent encapsulated lipid vesicle . The lipid vesicles are present in the solution of the first concentration, the apparatus further comprises a connected filtration system into the receiving vessel, the concentration of the filtration system lipid vesicles solution encapsulated the therapeutic agent 36. The apparatus of claim 35 , configured to increase the to a second concentration. 35. The device of claim 34 , wherein the therapeutic agent is selected from the group consisting of a protein, a plasmid, a nucleic acid, an antisense nucleic acid, a ribozyme, tRNA, snRNA, siRNA, pre-concentrated DNA, and an antigen. The apparatus of claim 34 , wherein the pump mechanism comprises a peristaltic pump. 35. The apparatus of claim 34 , wherein during mixing, the organic lipid solution is diluted serially in the presence of an aqueous solution. 35. The device of claim 34 , wherein the organic lipid solution comprises a therapeutic agent and the therapeutic agent is lipophilic. 35. The device of claim 34 , wherein the aqueous solution contains a therapeutic agent. Wherein the therapeutic agent The apparatus of claim 34, which is one of the anionic species and a cationic species. The process of claim 1, wherein the lipid vesicle is a liposome. The process of claim 1, wherein the lipid present in the organic lipid solution is solubilized in an organic solvent. 45. The process of claim 44, wherein the organic solvent is a lower alkanol. 46. The process of claim 45, wherein the lower alkanol is selected from the group consisting of methanol, ethanol, propanol, butanol, pentanol, isomers thereof, and combinations thereof. 46. The process of claim 45, wherein the lower alkanol comprises ethanol. The process of claim 1, wherein the lipid vesicles are produced at a shear rate between 0.075 L / min and 0.3 L / min. The process of claim 1, wherein the lipid vesicles are generated at a shear rate between 500 / s and 3300 / s. The process of claim 1, wherein the T connector is polypropylene or stainless steel. The process of claim 1, wherein the lipid present in the organic lipid solution comprises phospholipid, cholesterol, PEG-lipid and cationic lipid. 4. The process of claim 3, further comprising concentrating the lipid vesicles by tangential flow ultrafiltration. 35. The device of claim 34, wherein the lipid vesicle is a liposome. 35. The apparatus of claim 34, wherein the lipid present in the organic lipid solution is solubilized in an organic solvent. 55. The apparatus of claim 54, wherein the organic solvent is a lower alkanol. 56. The apparatus of claim 55, wherein the lower alkanol is selected from the group consisting of methanol, ethanol, propanol, butanol, pentanol, isomers thereof, and combinations thereof. 56. The apparatus of claim 55, wherein the lower alkanol comprises ethanol. 35. The apparatus of claim 34, wherein the lipid vesicles are generated at a shear rate between 0.075 L / min and 0.3 L / min. 35. The device of claim 34, wherein the lipid vesicles are generated at a shear rate between 500 / s and 3300 / s. 35. The apparatus of claim 34, wherein the T connector is polypropylene or stainless steel. 35. The device of claim 34, wherein the lipid present in the organic lipid solution comprises phospholipid, cholesterol, PEG-lipid and cationic lipid. 40. The apparatus of claim 36, further comprising concentrating the lipid vesicles by tangential flow ultrafiltration.

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